WO2002015963A1 - Intrakardiale blutpumpe - Google Patents

Intrakardiale blutpumpe Download PDF

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Publication number
WO2002015963A1
WO2002015963A1 PCT/EP2001/007953 EP0107953W WO0215963A1 WO 2002015963 A1 WO2002015963 A1 WO 2002015963A1 EP 0107953 W EP0107953 W EP 0107953W WO 0215963 A1 WO0215963 A1 WO 0215963A1
Authority
WO
WIPO (PCT)
Prior art keywords
pump
screen
blood
blood pump
opening
Prior art date
Application number
PCT/EP2001/007953
Other languages
German (de)
English (en)
French (fr)
Inventor
Thorsten Siess
Original Assignee
Impella Cardiosystems Ag
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Impella Cardiosystems Ag filed Critical Impella Cardiosystems Ag
Priority to US10/362,009 priority Critical patent/US7070555B2/en
Priority to DE50111817T priority patent/DE50111817D1/de
Priority to AU2001289640A priority patent/AU2001289640B2/en
Priority to AU8964001A priority patent/AU8964001A/xx
Priority to EP01969363A priority patent/EP1317295B1/de
Priority to JP2002520883A priority patent/JP4309126B2/ja
Publication of WO2002015963A1 publication Critical patent/WO2002015963A1/de

Links

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/40—Details relating to driving
    • A61M60/403—Details relating to driving for non-positive displacement blood pumps
    • A61M60/419—Details relating to driving for non-positive displacement blood pumps the force acting on the blood contacting member being permanent magnetic, e.g. from a rotating magnetic coupling between driving and driven magnets
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/10—Location thereof with respect to the patient's body
    • A61M60/122—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body
    • A61M60/126—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel
    • A61M60/13—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel by means of a catheter allowing explantation, e.g. catheter pumps temporarily introduced via the vascular system
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/10—Location thereof with respect to the patient's body
    • A61M60/122—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body
    • A61M60/165—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable in, on, or around the heart
    • A61M60/178—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable in, on, or around the heart drawing blood from a ventricle and returning the blood to the arterial system via a cannula external to the ventricle, e.g. left or right ventricular assist devices
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/20—Type thereof
    • A61M60/205—Non-positive displacement blood pumps
    • A61M60/216—Non-positive displacement blood pumps including a rotating member acting on the blood, e.g. impeller
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/40—Details relating to driving
    • A61M60/403—Details relating to driving for non-positive displacement blood pumps
    • A61M60/408—Details relating to driving for non-positive displacement blood pumps the force acting on the blood contacting member being mechanical, e.g. transmitted by a shaft or cable
    • A61M60/411—Details relating to driving for non-positive displacement blood pumps the force acting on the blood contacting member being mechanical, e.g. transmitted by a shaft or cable generated by an electromotor
    • A61M60/416—Details relating to driving for non-positive displacement blood pumps the force acting on the blood contacting member being mechanical, e.g. transmitted by a shaft or cable generated by an electromotor transmitted directly by the motor rotor drive shaft
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/50—Details relating to control
    • A61M60/508—Electronic control means, e.g. for feedback regulation
    • A61M60/538—Regulation using real-time blood pump operational parameter data, e.g. motor current
    • A61M60/554—Regulation using real-time blood pump operational parameter data, e.g. motor current of blood pressure
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/80—Constructional details other than related to driving
    • A61M60/802—Constructional details other than related to driving of non-positive displacement blood pumps
    • A61M60/81—Pump housings
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/80—Constructional details other than related to driving
    • A61M60/802—Constructional details other than related to driving of non-positive displacement blood pumps
    • A61M60/81—Pump housings
    • A61M60/816—Sensors arranged on or in the housing, e.g. ultrasound flow sensors
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2230/00—Measuring parameters of the user
    • A61M2230/04—Heartbeat characteristics, e.g. ECG, blood pressure modulation
    • A61M2230/06—Heartbeat rate only
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2230/00—Measuring parameters of the user
    • A61M2230/30—Blood pressure
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/10—Location thereof with respect to the patient's body
    • A61M60/122—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body
    • A61M60/126—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel
    • A61M60/148—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel in line with a blood vessel using resection or like techniques, e.g. permanent endovascular heart assist devices

Definitions

  • the invention relates to an intracardiac blood pump with a drive part containing a motor and a pump part which contains a pump wheel driven by the motor, at least one lateral throughflow opening being provided between the drive part and the pump part.
  • An intracardiac blood pump is a blood pump that is at least partially inserted into the heart to deliver blood from the heart into an artery, the pump being able to protrude through an operation opening of the heart.
  • Such intracardiac blood pumps have a maximum outer diameter of approximately 10-15 mm.
  • a special form of intracardiac blood pumps are intravascular blood pumps. These are inserted into the heart through the patient's vascular system, with the incision site distant from the heart. Intravascular blood pumps have a maximum diameter of about 8 mm and a rigid length of maximum 35 mm.
  • Intravascular blood pumps are known from WO 94/09835 (Jarvik) and EP 0 764 448 A2 (Jarvik).
  • An intravascular blood pump in which the outer diameter is only about 6 mm is described in WO 97/37696.
  • DE 198 21 307 Cl describes the right heart operation of an intravascular blood pump.
  • the blood pump is placed through the upper vena cava in the right atrium and a flexible cannula connected to the pump outlet extends through the tricuspid valve into the right ventricle and from there through the pulminal valve into the pulmonary artery.
  • the pump delivers from the right atrium into the pulmonary artery leading to the lungs.
  • the delivery rate is approx. 4.5 1 / min. required at physiological pressures (60 - 80 mm Hg).
  • This high delivery rate leads to high flow velocities in the side inlet opening between the drive part and the pump part, with the result that the blood pump generates a strong suction.
  • This allows the blood pump to suck onto the relatively thin wall of the right atrium.
  • suctioning has the consequence that the inflow opening is partially closed and the required blood flow cannot be reached, and on the other hand there is a risk of damage to the wall of the atrium.
  • tissue parts of the valve apparatus are sucked into the pump and block it hydraulically or block it mechanically.
  • the loss of function of a pump used to support the heart can have life-threatening consequences.
  • the present invention has for its object to provide an intracardiac blood pump that enables trouble-free continuous operation without the risk of sucking or sucking body matter.
  • the throughflow opening provided between the drive part and the pump part is covered with a screen which deflects the blood flow passing through the throughflow opening.
  • the blood flow passes through the flow opening in the radial direction with respect to the longitudinal axis of the blood pump, but this blood flow does not cause any radial pressure or suction. Rather, the pressure or suction is diverted from the screen in an axial direction with respect to the longitudinal axis of the blood pump.
  • the blood pump can be operated with different delivery directions depending on the direction of rotation of the motor and the shape of the pump wheel.
  • the throughflow opening between the drive part and the pump part is an inflow opening in one case and an outflow opening in the other case.
  • the screen which is arranged at a distance above the passage opening, has an advantageous effect on the operating behavior. If the throughflow opening acts as an inflow opening, the screen prevents the pump from being sucked into external parts by enlarging and spatially distributing the inlet opening. If the blood pump is operated in such a way that the throughflow opening forms the outflow opening, the screen effectively shortens the overall length of the blood pump, as later is explained. This enables the pump to be placed in the pulmonary artery without the risk of short circuit currents through the pulmonary valve.
  • a pressure sensor that measures the pressure outside and or inside of the pump part and determines the output of the pump based on the measured value, and further unusual operating conditions, such as "detects a cable closure and signals Such a sensor is covered by the screen so that there is no danger that the sensor will be pressed against a wall under the influence of the flow effects and thereby supply incorrect pressure values Actual suction pressure are separated. If a suction takes place, this is also recognized by the sensor.
  • FIG. 1 shows a first embodiment of the blood pump with a forward delivery direction as an intravascular right heart pump in operation in a heart
  • Fig. 2 is an enlarged view of the blood pump
  • FIG. 1 shows a side view of the blood pump according to FIG. 1,
  • Fig. 5 shows a second embodiment of the blood pump with the backward direction of delivery
  • Fig. 6 is an enlarged view of the blood pump
  • FIGs. 1 and 5 show a cross section through a human heart H.
  • the lower vena cava (inferior vena cava) and the upper vena cava (superior vena cava) open into the right atrium RA.
  • the tricuspid valve TK is located between the right atrium RA and the right ventricle RV.
  • the pulmonary valve PK is located between the right ventricle RV and the pulmonary artery PA.
  • the blood flows from the pulmonary artery PA via a branch to the left and right lungs and from there back into the left atrium LA and the left ventricle LV.
  • the aortic valve AK is located between the left ventricle LV and the aorta AO.
  • the blood pump 10 is an intravascular blood pump, that is to say an intracardiac blood pump, which can be pushed through a patient's blood vessel system in order to penetrate into the heart. At no point is the outside diameter larger than 10 mm.
  • the blood pump 10 has a drive part 11, one Pump part 12 and a flexible cannula 13 extending from the pump part 12, at the end of which there is an outlet opening 14 which is spanned by a sail-like tension element 15.
  • a catheter 16 extends from the rear end of the drive part 11 and has a lumen (not shown) for a guide wire and through which electrical lines for the power supply of the motor contained in the drive part 11 extend.
  • the cannula 13 can be temporarily stretched so that it can be pushed through the upper vena cava OHV. It is preloaded so that in the relaxed state it corresponds to that shown in Fig.
  • Pulmonary artery PA to be placed while the flow opening 17 is in the right atrium RA.
  • the construction of the blood pump basically corresponds to that of WO 97/37696, so that its internal structure is no longer explained in detail here.
  • the drive part points. an elongated one cylindrical housing in which the electric motor 19 is located.
  • Motor 19 is powered from an extracorporeal power source via electrical leads 20 that pass through catheter 16.
  • the lines 20 are connected to a control device which regulates the motor 19 in such a way that a desired pump power is obtained.
  • a pump wheel 22 sits on a shaft 21 of the motor 19, which rotates in the pump part 12 and axially drives the blood.
  • the pump part has a cylindrical pump ring 23 in which the pump wheel 22 is arranged. Between the drive part and the pump part 12 there are numerous through-flow openings 17 arranged circumferentially distributed, which in this exemplary embodiment are inlet openings.
  • the cannula 13 connects to the pump ring 23.
  • the cannula 13 is a flexible hose made of polyurethane with an elastic ring reinforcement.
  • a screen 24 is provided which at least partially covers the throughflow openings 17 and causes a deflection of the blood flow passing through the throughflow openings.
  • the screen 24 has a cylindrical closed wall 25, which covers the flow openings 17 over their entire length, and a front area with elongated slots 26 and a rear area with elongated slots 27.
  • the screen 24 is supported with its front end 28 on the Cannula 13 or the pump ring 23 and with its inwardly bent rear end 30 on the drive part 11, which it encloses. Under the screen 24, a flow path runs essentially along the entire length of the drive part 11, so that it is cooled by the blood flowing along it.
  • the blood pump of the Fign. 2 and 3 conveys in the forward direction, ie it sucks through the flow openings 17 and conveys to an end opening 31 at the end of the pump part 12 or at the transition from the pump part 12 to the cannula 13.
  • the closed wall 25 of the screen 24 distributes the suction effect on the elongated inlet slots 26 and 27 so that local suction tips are avoided.
  • a pressure sensor 33 is attached to the pump ring 23.
  • This pressure sensor is a differential pressure sensor which determines the difference between the pressures outside the pump ring 23 and inside the pump ring.
  • the pressure sensor 33 is connected via lines (not shown) to the lines passing through the catheter 16. It delivers pressure information to the extracorporeal control unit, which makes it possible to use a computer to determine the current delivery rate of the pump, for example to regulate the delivery rate or delivery rate for a specific work.
  • the sensor 33 also detects a pressure jam or local seizure, which is then registered as an abnormal operating condition.
  • the sensor 33 is located at a distance below the screen 24, so that the screen prevents foreign bodies from lying against the sensor from the outside. The sensor 33 always determines the true external pressure surrounding the pump ring 23 as the external pressure.
  • the sensor is arranged under the screen 24 in the same compartment as the pressure flow opening 17, so that both are exposed to the same pressure. Sucking or seizing of the pump can therefore be detected by the sensor and used sensor-based to regulate the delivery rate of the pump.
  • the pressure of the pressure sensor 33 can be used not only to monitor and control the pump operation but also to determine the proper placement of the pump in the heart.
  • a pressure transmission tube 32 extends along the cannula 13 and is open at the distal end 34 (FIG. 1).
  • the pressure transmission tube 32 is embedded in the housing of the drive part 11 and continues in the catheter 16 (FIG. 2). Its extracorporeal end is connected to a pressure measuring device that evaluates the pressure.
  • the screen 24 surrounds the drive part 11 and the pump part 12 with a radial distance of 1 to 2 mm.
  • the screen 24 forms the outer jacket of the blood pump 10. Its outer diameter is approximately 8 mm and its rigid length is approximately 40 mm.
  • the screen 24 is made of thin steel, in which the inlet slots 26, 27 are cut out by laser cutting processes.
  • the blood pump reduces the tendency to suction on the easily deformable material of the right atrium through the screen 24 surrounding the flow openings 17. Damage to the tricuspid valve TK and the valve apparatus with the consequence of the risk of the pump being stopped is avoided.
  • the pressure sensor 33 is exposed under the screen 24. It cannot be separated from the suction area, so that any seizure of the blood pump by the sensor is also recognized. 2, the blood flow that is radial through the Inlet slots 26, 27 occurs, first deflected in the axial direction before it radially passes through the flow opening 17.
  • the blood pump 10 delivers here in the reverse direction, that is to the catheter 16.
  • the cannula 13a which adjoins the drive part 11, is straight in this case.
  • At the free end of the cannula 13a "is the suction port 35.
  • the pump is inserted through an incision 36 at or below the branch of the pulmonary artery PA in the pulmonary artery.
  • the distance between the incision 36 of the pulmonary valve PK is relatively short in many cases.
  • the Blood pump 10 should be housed completely within the pulmonary artery PA, with only the cannula 13a projecting through the pulmonary valve PK.
  • the screen 24a on the blood pump 10 makes it possible to shorten the blood pump to a certain extent, the screen 24a with a part of the The length of the blood pump protrudes through the pulmonary valve and the outlet opening 37 is located approximately in the middle of the length of the drive part 11. This considerably shortens the rigid length of the pump which is accommodated in the pulmonary artery.
  • the structure of the blood pump according to FIG. 5 is shown in detail in FIG. 6.
  • the shield 24a sits sealingly on the circumference of the pump ring 23 or on the wall of the cannula 13a connected to the pump ring.
  • the screen 24a has a transition 39 in which it widens to the diameter of a cylindrical section 40 which extends over the drive part 11 to approximately the middle of the length of the drive part.
  • the cylindrical section 40 ends in an annular outlet opening 37.
  • the blood flows out of the cannula 13a through the end opening 31 of the pump ring 23, in which the rotating pump wheel is located.
  • the blood then continues to flow through the lateral throughflow openings into the interior of the closed-walled screen 24a.
  • the screen 24a is only open at the axially directed outlet opening 37.
  • the blood flow which radially emerges from the throughflow opening 17, is deflected in the axial direction by the screen 24a. Since the outlet opening is not located at the front end of the blood pump 10 but in its central region, the overall operational length of the pump is shortened.
  • Drive part 11 and pump part 12 have approximately the same diameter.
  • the screen 24a surrounds the drive part 11 at a radial distance.
  • a pressure sensor 33 is also provided on the pump ring 23.
  • the pressure sensor 33 is a differential pressure sensor which is arranged in an opening of the pump ring. The inner sensor surface is exposed to the internal pressure of the pump part and the outer sensor surface is connected to the interior of the screen 24a and is thus exposed to the outlet pressure of the pump.
  • the blood pump 10 of the two exemplary embodiments described are fundamentally the same in structure. They differ in the different delivery directions that can be realized by appropriate electrical control and design of the pump part.

Landscapes

  • Health & Medical Sciences (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Engineering & Computer Science (AREA)
  • Cardiology (AREA)
  • Biomedical Technology (AREA)
  • Anesthesiology (AREA)
  • Mechanical Engineering (AREA)
  • Hematology (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Vascular Medicine (AREA)
  • External Artificial Organs (AREA)
PCT/EP2001/007953 2000-08-18 2001-07-10 Intrakardiale blutpumpe WO2002015963A1 (de)

Priority Applications (6)

Application Number Priority Date Filing Date Title
US10/362,009 US7070555B2 (en) 2000-08-18 2001-07-10 Intracardiac blood pump
DE50111817T DE50111817D1 (de) 2000-08-18 2001-07-10 Intrakardiale blutpumpe
AU2001289640A AU2001289640B2 (en) 2000-08-18 2001-07-10 Intracardiac blood pump
AU8964001A AU8964001A (en) 2000-08-18 2001-07-10 Intracardiac blood pump
EP01969363A EP1317295B1 (de) 2000-08-18 2001-07-10 Intrakardiale blutpumpe
JP2002520883A JP4309126B2 (ja) 2000-08-18 2001-07-10 心臓内血液ポンプ

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE10040403A DE10040403A1 (de) 2000-08-18 2000-08-18 Intrakardiale Blutpumpe
DE10040403.0 2000-08-18

Publications (1)

Publication Number Publication Date
WO2002015963A1 true WO2002015963A1 (de) 2002-02-28

Family

ID=7652873

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/EP2001/007953 WO2002015963A1 (de) 2000-08-18 2001-07-10 Intrakardiale blutpumpe

Country Status (6)

Country Link
US (1) US7070555B2 (ja)
EP (1) EP1317295B1 (ja)
JP (1) JP4309126B2 (ja)
AU (2) AU8964001A (ja)
DE (2) DE10040403A1 (ja)
WO (1) WO2002015963A1 (ja)

Cited By (4)

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WO2006133209A1 (en) * 2005-06-06 2006-12-14 The Cleveland Clinic Foundation Blood pump
WO2012075152A1 (en) 2010-12-01 2012-06-07 Abiomed, Inc. Radiopaque cannula marker
EP3189862A1 (en) 2010-12-01 2017-07-12 Abiomed, Inc. Loading guide lumen
US11938311B2 (en) 2016-09-01 2024-03-26 Abiomed, Inc. Anti-suction blood pump inlet

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US6889082B2 (en) 1997-10-09 2005-05-03 Orqis Medical Corporation Implantable heart assist system and method of applying same
US7022100B1 (en) 1999-09-03 2006-04-04 A-Med Systems, Inc. Guidable intravascular blood pump and related methods
US7494477B2 (en) * 2003-09-02 2009-02-24 Pulsecath B.V. Catheter pump, catheter and fittings therefore and methods of using a catheter pump
WO2005028872A2 (en) 2003-09-18 2005-03-31 Myrakelle, Llc Rotary blood pump
US7393181B2 (en) 2004-09-17 2008-07-01 The Penn State Research Foundation Expandable impeller pump
US7347810B2 (en) 2004-10-01 2008-03-25 Stamos Thomas A Device for draining the coronary sinus
DE102004049986A1 (de) * 2004-10-14 2006-04-20 Impella Cardiosystems Gmbh Intrakardiale Blutpumpe
US7878967B1 (en) * 2005-10-06 2011-02-01 Sanjaya Khanal Heart failure/hemodynamic device
WO2007090050A2 (en) * 2006-01-27 2007-08-09 Circulite, Inc. Heart assist system
EP1996252B1 (en) 2006-03-23 2016-05-11 The Penn State Research Foundation Heart assist device with expandable impeller pump
AU2007233078B2 (en) 2006-03-31 2011-11-24 Thoratec Corporation Rotary blood pump
KR101115493B1 (ko) 2006-06-16 2012-03-13 에이엠에스 리써치 코오포레이션 골반질병치료용 임플란트, 도구 및 방법
ES2528902T3 (es) 2006-08-30 2015-02-13 Circulite, Inc. Dispositivos y sistemas para establecer el flujo sanguíneo complementario en el sistema circulatorio
US8333686B2 (en) * 2006-08-30 2012-12-18 Circulite, Inc. Cannula insertion devices, systems, and methods including a compressible member
US7905823B2 (en) * 2006-08-30 2011-03-15 Circulite, Inc. Devices, methods and systems for establishing supplemental blood flow in the circulatory system
JP5457182B2 (ja) * 2006-09-14 2014-04-02 サーキュライト・インコーポレーテッド 血管内血液ポンプおよびカテーテル
US9028392B2 (en) * 2006-12-01 2015-05-12 NuCardia, Inc. Medical device
US11064964B2 (en) 2007-03-08 2021-07-20 Sync-Rx, Ltd Determining a characteristic of a lumen by measuring velocity of a contrast agent
US11197651B2 (en) 2007-03-08 2021-12-14 Sync-Rx, Ltd. Identification and presentation of device-to-vessel relative motion
US9629571B2 (en) 2007-03-08 2017-04-25 Sync-Rx, Ltd. Co-use of endoluminal data and extraluminal imaging
US8781193B2 (en) 2007-03-08 2014-07-15 Sync-Rx, Ltd. Automatic quantitative vessel analysis
WO2008107905A2 (en) 2007-03-08 2008-09-12 Sync-Rx, Ltd. Imaging and tools for use with moving organs
US10716528B2 (en) 2007-03-08 2020-07-21 Sync-Rx, Ltd. Automatic display of previously-acquired endoluminal images
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US20030187322A1 (en) 2003-10-02
DE50111817D1 (de) 2007-02-15
EP1317295B1 (de) 2007-01-03
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US7070555B2 (en) 2006-07-04

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